Method for determining the power of an intraocular lens

ABSTRACT

For the pre-operative calculation of the power of an intraocular lens, three input parameters are needed: the axial length of the eye (AL), the refractive power of the cornea, and the distance between the front of the cornea and the back focal plane of the intraocular lens, the so-called effective lens position (ELP). The invention shows a novel approach to the determination of the ELP.

PRIORITY

This application is a continuation of PCT/EP2008/004406, filed Jun. 3, 2008. This application claims priority to U.S. Provisional Application, Ser. No. 60/933,012, filed Jun. 4, 2007, the disclosure of which is incorporated herein by reference.

TECHNICAL FIELD

Biometry, particularly measurement of geometrical parameters in the anterior segment, for the calculation of the refractive power of intraocular lenses (IOL).

BACKGROUND OF THE INVENTION

For the pre-operative calculation of the power of an intraocular lens, three input parameters are needed: the axial length of the eye (AL), the refractive power of the cornea, and the distance between the front of the cornea and the back focal plane of the intraocular lens, the so-called effective lens position (ELP).

To a good approximation, the post-operative axial length can be substituted by the corresponding value measured pre-operatively. The axial length can be measured either ultrasonically or optically using partial coherence interferometry (PCI). Also—at least for eyes that have not undergone keratorefractive surgery—the post-op corneal power can be predicted based on the pre-op measurement of the front surface corneal radii. This prediction is based on assumptions about the corneal index of refraction and the ratio of front and back surface corneal radii. Keratometry can be measured using manual or automatic optical keratometers, or extracted from a corneal topography obtained via Placido ring projection.

The effective lens position, on the other hand, is inherently a post-operative value. In fact the final position of an IOL does not manifest itself until a number of weeks after surgery, when the capsular bag has shrunk around the implant. A pre-op parameter the ELP approximately corresponds to is the distance from the front of the cornea to the front of the crystalline lens, the so-called anterior chamber depth (ACD). The ACD can be measured ultrasonically or optically using slit projection, or it can be predicted based on the diameter of the clear cornea (the so-called white-to-white distance, WTW) and its central curvature. In commonly used IOL calculation formulas, the ELP is predicted using an empirical fit of several parameters such as ACD and AL. Olsen has suggested that the prediction can be improved by inclusion of additional parameters such as the lens thickness (LT), corneal radius, and pre-op refraction (Acta Ophthalmol. Scand. 2007: 85: 84-87). Most commonly used IOL calculation formulas are based on the same vergence formula to model focusing by the intraocular lens; they only differ in the method for predicting ELP.

SUMMARY OF THE INVENTION

It is the purpose of this invention to provide a better ELP prediction by measuring a pre-op quantity that correlates closely to the post-op position of the IOL. In one preferred embodiment, an OCT device is used to indentify the iris root. The axial separation (ACD′) between the front surface of the cornea and the plane of the iris root is then determined. The power of the intraocular lens is determined using the measured axial separation together with other measured parameters and empirically determined lens constants.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a cross sectional view of the eye.

FIG. 2 is a cross sectional view of the eye illustrating the axial distance (ACD′) between the front surface of the cornea and the plane of the iris root.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

As seen in the attached FIG. 1, in cross-sectional images of the anterior segment of the eye obtained by optical coherence tomography (OCT) at infrared wavelengths (e.g., 1310 nm) a strongly scattering layer 10 is visible near the back surface of the iris. This structure is commonly interpreted as the iris pigment epithelium. On the other hand, it has also been suggested that this scattering region may correspond to the iris dilator muscle.

At the periphery, the absorbing layer ends at a well-defined radial position (location 12 in FIG. 1), which is anatomically close to, or co-located with the iris root. In a meridional cross sectional OCT scan of the cornea the two peripheral end points of the scattering layer in the iris can be used to uniquely identify two iris root points. A line connecting the two iris root points can be used to define a root-to-root line. This line is shown as item 20 in FIG. 2.

The separation of the root-to-root line from the front of the cornea 16 can be used to define a modified anterior chamber depth parameter ACD′ (see FIG. 2). This can be defined in one of several different ways. Most simply, ACD′ can be defined as the longest perpendicular distance from the root-to-root line to the front surface of the cornea. If the patient fixates in a direction parallel to the direction of the OCT scan during measurement, the line of sight can be uniquely identified in the acquired cross sectional image. ACD′ can then alternatively be defined as the longest distance from the root-to-root line to the corneal front surface, measured parallel to the line of sight. Finally, the inner limits of the iris in the OCT scan can be used to mark the mid-point of the pupil along the root-to-root line. As a third alternative, the parameter ACD′ can be measured from this mid-point to the corneal front surface, in a direction parallel to the line of sight.

The parameter ACD′ can be used to predict the post-op effective lens position. Like with presently used formulas this can be done by empirically determining regression coefficients for a set of parameters, such as ACD′, AL, and/or LT. Other measured parameters can include the two central radii of the corneal front surface. The prediction of ELP thus obtained can be used in IOL calculation formulas together with empirical lens constants.

Another possible approach relies on a measurement associated with a region located at the most anterior portion of a highly scattering layer posterior to the sclera (location 14 of FIG. 1). This layer is presumably a pigmented layer along the posterior boundary of the ciliary muscle. Similar to the approach shown in FIG. 2, a line connecting these two opposing points (14) can be drawn and the separation between this line and the front of the cornea (ACD″—not shown) can be defined and used to predict the IOL position after surgery. The value for ACD″ can be used alone or in conjunction with the value for ACD′.

As is well known in the art, the determination of regression coefficients requires large data sets and produce formulas that have limited physical interpretation. The larger number of measurements to be included and the more complex the formula, the more data is required to develop those formulas. This can especially be a drawback in the modification of IOL calculation formulas for newly developed IOL's. The IOL calculation formula may instead take the form of regression formulas to calculate intermediate parameters such as the position of the IOL equator and the effective power of the lens. For example, the ELP is determined by a combination of anatomical features, such as the distance from the corneal vertex to the sulcus, by the design of the IOL and by surgical technique. Various surrogate measurements may be combined. For example the ACD′ characterizes the position of the iris root. A combination of the traditional ACD, LT, anterior radius of curvature of the crystalline lens, and possibly also posterior radius of curvature of the crystalline lens, characterize the crystalline lens equator. These and other surrogate measurements (including ACD″) can be combined into a regression formula for predicting the position of the IOL equator. The ELP prediction can then be calculated as a combination of the optical power, derived from the radii of curvature and index of refraction, the predicted IOL equator. The resulting ELP estimate can be integrated into an IOL calculation formula.

A particular embodiment of the inventive method consists in the following sequence: The axial length (AL) of a patient eye is measured using partial coherence interferometry (PCI), the modified anterior chamber depth ACD′ is determined using optical coherence tomography (OCT) and the corneal power is determined using a suitable keratometric setup. The keratometric setup can be a stand-alone keratometer or integrated into a combination device such as the IOLMaster. After obtaining these measurements, the values are processed together with the desired target refraction using the Haigis-Formula to determine the required power of an intraocular lens.

In  the  Haigis-Formula ${D\; L} = {\frac{n}{L - d} - \frac{n}{{n/z} - d}}$ with $z = {{{D\; C} + {\frac{ref}{1 - {{ref}\mspace{14mu} {dBC}}}\mspace{14mu} {and}\mspace{14mu} D\; C}} = \frac{{nC} - 1}{R\; C}}$

where

-   DL: IOL-refraction -   DC: cornea refraction -   RC: cornea tradius -   nC: refractive index of the cornea -   ref: refraction to be obtained after surgery -   dBC: spectacle distance from cornea -   d: optical anterior chamber depth ACD -   L: Eye length -   n: refractive index of the eye (1.336)     d is normally predicted using a function based on a multi-variable     regression analysis from a large sample of surgeon and IOL-specific     outcomes for a wide range of axial lengths (AL) and anterior chamber     depths (ACD).

In the preferred embodiment, the modified anterior chamber depths parameter ACD′ (or ACD″) would be used in place of ACD in the regression fit.

In other common IOL formulas an expression equivalent to d is used too as the table shows:

SRK/T d=A-constant

Hoffer Q d=pACD

Holladay 1 d=Surgeon Factor

Holladay 2 d=ACD

Also in these formulas d may be substituted by the modified anterior chamber depth ACD′ (or ACD″).

The invention is not limited to the embodiments described, also other uses of the measured values ACD′ or ACD″ for IOL calculation fall within the scope of protection. 

1. A method for calculating the power of an intraocular lens comprising the steps of: measuring an axial separation (ACD′) between the front surface of the cornea and the plane of the iris root; and determining the power of the intraocular lens using the measured axial separation together with other measured parameters and empirically determined lens constants.
 2. The method of claim 1, where the plane of the iris root is determined using an optical coherence measurement at an infrared wavelength.
 3. The method of claim 2, where the optical coherence measurement consists of one or more meridional scans.
 4. The method of claim 3, where the location of the iris root is measured as the outer end points of the strongly scattering layer in the back of the iris.
 5. The method of claim 4, where the other measured parameters include the axial eye length and at the two central radii of the corneal front surface.
 6. The method of claim 5, where the other measured parameters further include the lens thickness.
 7. A method for calculating the power of an intraocular lens comprising the steps of: measuring an axial separation (ACD″) between the front surface of the cornea and a line connecting the posterior edge of the ciliary body; and determining the power of the intraocular lens using the measured axial separation together with other measured parameters and empirically determined lens constants.
 8. A method for calculating the power of an intraocular lens comprising the steps of: determining the location of the crystalline lens equator based on a combination of the anterior chamber depth, crystalline lens thickness and the anterior radius of curvature of the crystalline lens; using the determined location of the crystalline lens equator to predict the location of the intraocular lens equator; and using the predicted location of the intraocular lens equator in a calculation to determine the appropriate power of an intraocular lens.
 9. A method as recited in claim 8, wherein said step of determining the location of the crystalline lens equator is further based on the posterior radius of curvature of the crystalline lens.
 10. A method as recited in claim 8, wherein the step of predicting the location of the intraocular lens equator is further based on a determination of the location of the iris root.
 11. A method of determining the power of an intraocular lens comprising the steps of: generating image information of the eye using an optical coherence tomography systems; identifying the location of the iris root based on the image information; and determining the power of the intraocular lens based on the location of the iris root coupled additional measurements including the anterior cornea radius and axial eye length.
 12. A method as recited in claim 11, wherein the location of the iris root is used to calculate the effective intraocular lens position and wherein the calculated effective intraocular lens position is used to determine the power of the intraocular lens.
 13. A method as recited in claim 11, wherein said additional measurements include at least one of the posterior corneal radius and anterior chamber depth.
 14. A method of determining the power of an intraocular lens comprising the steps of: measuring the crystalline lens radius or radii or thickness with one of an optical coherence tomography (OCT) system, a slit projection system and an Ultrasound system; and determining the power of the intraocular lens based on said measurements and additional measurements including one or more of the axial eye length, anterior cornea radius, posterior corneal radius, anterior chamber depth (ACD).
 15. A method as recited in claim 14, where said determining step is performed using a formula or a ray-tracing algorithm.
 16. A method as recited in claim 14, wherein said determining step is further based on a calculation of the effective lens position (ELP), wherein the ELP is derived from one or more additional parameters including the crystalline lens radius and the crystalline lens thickness. 